Micro-optical surgical probes and micro-optical probe tips and methods of manufacture therefor

ABSTRACT

Described are various embodiments of micro-optical surgical probes and micro-optical probe tips and methods of manufacture therefor. In some embodiments, multichannel micro-optical probe tip structures are directly manufactured upon respective optical channel waveguides, or again manufactured to integrally define respective optical coupling to these waveguides. In some embodiments, micro-optical probe tip structures are manufactured via a 3D laser printing process. Specific embodiments include, but are not limited to, spectroscopic or particularly Raman spectroscopy probes and their associated multichannel probe tip structures, and multichannel endoscopes.

FIELD OF THE DISCLOSURE

The present disclosure relates to medical instruments, tools andsystems, and, in particular, to micro-optical surgical probes andmicro-optical probe tips and methods of manufacture therefor.

BACKGROUND

Various optical surgical probes, tools and instruments have beendeveloped to improve the accuracy and ultimate success of a givensurgical procedure. Known imaging tools for visually closed-accesssurgical procedures, for example those channelled through an anatomicallumen (e.g. vascular, intestinal procedures), may include fibre opticscopes, optical coherence tomography (OCT) probes, micro ultrasoundtransducers and the like, wherein a generally flexible tool is insertedand channelled to a surgical site of interest. Similar tools forvisually closed-access surgical procedures, for example those introducedwithin an open cavity such those involved in port-based surgicalprocedures or the like, may also include fibre optic scopes, in someinstances, provided by way of a substantially rigid scope body that canbe visually or externally tracked via a procedural imaging and trackingsystem, for example.

One particular impediment to the development of improved opticalsurgical tools, particularly as surgical procedures are continuouslyseeking to reduce or minimize required surgical access areas, is thelack of small-diameter optical probes and their related opticalcomponents. This challenge is only compounded for surgical probesinvolving multiple optical channels and/or paths.

This background information is provided to reveal information believedby the applicant to be of possible relevance. No admission isnecessarily intended, nor should be construed, that any of the precedinginformation constitutes prior art or forms part of the general commonknowledge in the relevant art.

SUMMARY

The following presents a simplified summary of the general inventiveconcept(s) described herein to provide a basic understanding of someaspects of the disclosure. This summary is not an extensive overview ofthe disclosure. It is not intended to restrict key or critical elementsof embodiments of the disclosure or to delineate their scope beyond thatwhich is explicitly or implicitly described by the following descriptionand claims.

A need exists for micro-optical surgical probes and micro-optical probetips and methods of manufacture therefor, that overcome some of thedrawbacks of known techniques, or at least, provides a usefulalternative thereto. Some aspects of this disclosure provide examples ofsuch probes, tools and methods.

For instance, in accordance with some aspects of the present disclosure,there is provided a medical probe for internally probing tissue or fluidwithin a body, the probe comprising: an elongate probe body having anexternal end, and an insertable end to be inserted within the bodytoward the tissue or fluid to be probed; an illumination waveguidedisposed along the probe body to output optical illumination from theinsertable end toward the tissue or fluid to be probed; a collectionwaveguide disposed along the body to collect, from the insertable end,an optical response of the tissue or fluid to the output opticalillumination; and an optical probe tip structure integrally fabricatedatop both the illumination waveguide and the collection waveguide tooptically relay the output optical illumination from the illuminationwaveguide and the optical response to the collection waveguide.

In one embodiment, the illumination waveguide is a core illuminationwaveguide, the collection waveguide comprises a set of circumferentiallydisposed collection waveguides circumferentially disposed around andparallel to the core illumination waveguide, and the optical probe tipstructure is optically fabricated atop and to optically couple with boththe core illumination waveguide and the circumferentially disposedcollection waveguides.

In one embodiment, the optical response is defined by a designatedoptical collection spectrum, and the optical probe tip structure furthercomprises a collection wavelength-selective element defined within acollection optical path of the optical response toward the collectionwaveguide to at least partially confine the optical response to thedesignated optical collection spectrum.

In one embodiment, the collection wavelength-selective element comprisesan optical coating deposited upon a surface previously fabricated withinthe optical path.

In one embodiment, the optical illumination is defined by a designedoptical illumination spectrum, and the optical probe tip structurefurther comprises an illumination wavelength-selective element definedwithin an illumination optical path of the optical illumination from theillumination waveguide to at least partially confine the opticalillumination to the designated optical illumination spectrum.

In one embodiment, the illumination wavelength-selective elementcomprises an optical coating deposited upon a surface previouslyfabricated within the illumination optical path.

In one embodiment, the optical probe tip structure comprises amonolithic structure fabricated of light-transmissive material andintegrally shaped to optically couple to both the illumination waveguideand the collection waveguide and optically relay the opticalillumination and optical response therefrom and thereto, respectively.

In one embodiment, the optical probe tip structure is at least partiallymanufactured by a micro-optical 3D printing process executed to directlymanufacture the probe tip structure atop both the optical illuminationwaveguide and the optical collection waveguide.

In one embodiment, the micro-optical 3D printing process is a two-photonlaser 3D printing process.

In one embodiment, the optical probe tip structure further comprises areflective surface for redirecting at least one of the opticalillumination and the optical response.

In one embodiment, the reflective surface comprises a reflective coatingdisposed on a previously fabricated probe tip surface.

In one embodiment, the optical probe tip structure is at least partiallyfabricated to define one or more beam shaping elements.

In one embodiment, the beam shaping elements are at least partiallydefined by a lens grating integrally fabricated within the optical probetip structure and coupling to with at least one of the collectionwaveguide and the illumination waveguide.

In one embodiment, the beam shaping elements are at least partiallydefined by a set sequential lens sequentially coupling with at least oneof the collection waveguide and the illumination waveguide.

In one embodiment, the optical probe tip structure is fabricated tointegrally define respective optical engagement paths for each of theillumination waveguide and the collection waveguide to optimize opticalengagement therewith upon fabrication.

In one embodiment, the probe is a disposable probe to be operativelycoupled at the external end thereof to a reusable device housing anillumination light source and an optical detector, wherein coupling theexternal end to the reusable device automatically optically couples thelight source to the illumination waveguide and the collection waveguideto the optical sensor.

In one embodiment, a diameter of the probe tip structure is no greaterthan 2 mm.

In one embodiment, a diameter of the probe tip structure is no greaterthan 1 mm.

In accordance with other aspects, there is a provided a method formanufacturing a medical probe comprising: assembling a multichannelfiber bundle comprising at least two optical fibers associated withdistinct optical probe channels; micro-fabricating a common monolithicoptical probe tip structure via a 3D laser printing process toconcurrently engage and respectively optically couple the optical probetip structure with a common distal end of each of the at least twooptical fibers in ultimately defining respective predesigned opticalchannel paths within the probe tip structure.

In one embodiment, the micro-fabricating comprises micro-fabricating thestructure directly upon the common distal end of the at least twooptical fibers.

In one embodiment, the micro-fabricating comprises micro-fabricatingrespective probe tip ports or waveguides to controllably engage andrespectively optically couple the optical probe tip structure with eachof the at least two optical fibers.

In one embodiment, the micro-fabricating comprises micro-fabricating acommon probe tip port to controllably engage the fiber bundle andrespectively optically couple the optical probe tip structure with eachof the at least two optical fibers.

In one embodiment, the micro-fabricating comprises micro-fabricating arespective lens element for each of the respective predesigned opticalchannel paths.

In one embodiment, the at least two optical fibers comprise at least oneillumination fiber for operative coupling to an illumination lightsource in relaying illumination via the probe tip structure, and atleast one collection fiber for operative coupling to a detector incollecting light in response to the illumination, wherein the methodfurther comprises: defining one or more wavelength-selective featureswithin the optical probe tip structure to govern a spectral responsethereof along a corresponding one of the predesigned optical channelpaths.

In one embodiment, the defining comprises depositing awavelength-selective coating upon a designated probe tip structuresurface fabricated to intersect the corresponding one of the predesignedoptical channel paths.

In one embodiment, the surface comprises an internal surface.

In one embodiment, the defining comprises integrally fabricating atexturized wavelength-selective surface within the probe tip structureto intersect at least one of the predesigned optical channel paths.

In one embodiment, the micro-fabricating comprises fabricating a beamsteering surface within the optical probe tip structure to redirect atleast one of the predesigned optical channel paths at an angle relativeto the fiber bundle.

In accordance with other aspects, there is provided a medical probe forinternally probing tissue or fluid within a body, the probe comprising:an elongate probe body having an external end, and an insertable end tobe inserted within the body toward the tissue or fluid to be probed; anillumination waveguide disposed along the probe body to output opticalillumination from the insertable end toward the tissue or fluid to beprobed; a collection waveguide disposed along the body to collect, fromthe insertable end, an optical response of the tissue or fluid to theoutput optical illumination; and a monolithically fabricatedmultichannel optical probe tip structure fabricated oflight-transmissive material and integrally formed to optically engageboth the illumination waveguide and the collection waveguide tooptically relay the output optical illumination from the illuminationwaveguide and the optical response to the collection waveguide.

In one embodiment, the monolithically fabricated optical structure is atleast partially fabricated via a micro-optical 3D laser printingprocess.

In one embodiment, the micro-optical 3D laser printing process isdirectly implemented atop both the optical illumination waveguide andthe optical collection waveguide to integrally fabricate themonolithically fabricated optical structure thereon.

In one embodiment, the optical response is defined by a designatedoptical response spectrum; and wherein the optical probe tip structurefurther comprises a collection wavelength-selective element definedwithin the monolithically fabricated optical structure along acollection optical path of the optical response to at least partiallyconfine the optical response within the collection waveguide to thedesignated optical collection spectrum.

In one embodiment, the collection wavelength-selective element comprisesan optical coating deposited upon an internal monolithically fabricatedsurface.

In one embodiment, the optical illumination is defined by a designedoptical illumination spectrum, and the optical probe tip structurefurther comprises an illumination wavelength-selective element definedwithin the monolithically fabricated optical structure along anillumination optical path of the optical illumination to at leastpartially confine the optical illumination within the illuminationwaveguide to the designated optical illumination collection spectrum.

In one embodiment, the illumination wavelength-selective elementcomprises an optical coating deposited upon an internal monolithicallyfabricated surface.

In one embodiment, the illumination waveguide is a core illuminationwaveguide and wherein the collection waveguide comprises a set ofcircumferentially disposed collection waveguides circumferentiallydisposed around and parallel to the core illumination waveguide.

In one embodiment, the monolithically fabricated optical probe tipstructure is fabricated to integrally define respective opticalengagement ports or waveguides for each of the illumination waveguideand the collection waveguide to optimize optical engagement therewithupon assembly.

In one embodiment, the monolithically fabricated optical probe tipstructure defines one or more light shaping elements.

In one embodiment, the one or more light shaping elements are integrallyformed to focus the output optical illumination.

In one embodiment, the one or more light shaping elements are integrallyformed to collect and focus the optical response into the collectionwaveguide.

In one embodiment, the monolithically fabricated optical probe tipstructure at least partially defines one or more optical steeringelements to redirect at least one of the output illumination or theoptical response relative to the elongate probe body.

In one embodiment, the one or more optical steering elements comprise areflective surface for concurrently laterally redirecting the outputillumination and the optical response to peripherally probe the tissueor fluid.

In one embodiment, the reflective surface is defined by an integrallyformed surface coated with a reflective coating.

In one embodiment, the illumination waveguide and the collectionwaveguide to define a first optical probe; the medical probe furthercomprises a second optical probe defined by a distinct waveguidedisposed along the body to relay or collect secondary light via adistinct optical feature defined within the optical probe tip structure;and the monolithically fabricated optical probe tip structure is furtherintegrally formed to define the distinct optical feature and tooptically engage the distinct waveguide.

In one embodiment, the monolithically fabricated optical probe tipstructure at least partially defines a first optical steering element toredirect the output illumination and the optical response relative tothe elongate probe body in defining a first external optical probe port;and the monolithically fabricated optical probe tip structure at leastpartially defines a second optical steering element to redirect thesecondary light relative to the elongate probe body in defining a secondexternal optical probe port.

In one embodiment, the at least one of the first or second opticalsteering element comprises a reflective surface defined by an integrallyformed surface coated with a reflective coating.

In one embodiment, the probe is a disposable probe to be operativelycoupled at the external end thereof to a reusable device housing anillumination light source and an optical detector, wherein coupling theexternal end to the reusable device automatically optically couples thelight source to the illumination waveguide and the collection waveguideto the optical sensor.

In accordance with other aspects, there is provided a surgical devicefor operating on fluid or tissue within a body, the device comprising: asurgical tool having an elongate tool body and an operable tool tiptoward a distal tool end thereof that is insertable within the body tooperate on the fluid or tissue; and an optical probe as defined abovefor concurrently probing the fluid or tissue within the body.

In one embodiment, the surgical tool comprises at least one of a suctiontool, a resection tool or a pointing tool.

In one embodiment, the surgical device further comprises a set offiducial markers externally trackable via an external surgical trackingsystem.

In accordance with other aspects, there is provided a medical probe forinternally probing tissue or fluid within a body, the probe comprising:an elongate probe body having an external end, and an insertable end tobe inserted within the body toward the tissue or fluid to be probed; anillumination waveguide disposed along the probe body to output opticalillumination from the insertable end toward the tissue or fluid to beprobed; an optical sensor disposed at the insertable end to collecttherefrom an optical response of the tissue or fluid to the outputoptical illumination; and a monolithically fabricated multichanneloptical probe tip structure fabricated of light-transmissive materialand integrally formed to optically engage both the illuminationwaveguide and the optical sensor to optically relay the output opticalillumination from the illumination waveguide and the optical response tothe sensor.

In accordance with other aspects, there is provided a medical probe forinternally probing tissue or fluid within a body, the probe comprising:an elongate probe body having an external end, and an insertable end tobe inserted within the body toward the tissue or fluid to be probed; anillumination system to output optical illumination from the insertableend toward the tissue or fluid to be probed; a multichannel opticalsensor disposed to collect, from the insertable end, respective opticalchannel responses of the tissue or fluid to the output opticalillumination; and a monolithically fabricated multichannel optical probetip structure fabricated of light-transmissive material and integrallyformed to optically engage the multichannel sensor to respectivelyoptically relay each of the optical channel response to the multichannelsensor.

In one embodiment, the medical probe further comprises a multichanneloptical waveguide disposed along the body to collect, from theinsertable end, the respective optical channel responses and relay theoptical channel responses to the multichannel sensor; wherein themonolithically fabricated multichannel optical probe tip structure isintegrally formed to optically engage the multichannel optical waveguideto respectively optically relay each of the optical channel responsealong respective waveguide channels to the multichannel sensor.

In one embodiment, the multichannel sensor comprises one of a singlemultichannel sensor or multiple channel-specific optical sensors.

In accordance with yet another aspect, there is provided a medical probefor internally probing or operating on tissue or fluid within a body,the probe comprising: an elongate probe body having an external end, andan insertable end to be inserted within the body toward the tissue orfluid to be probed or operated on; an illumination waveguide disposedalong the probe body to output optical illumination from the insertableend toward the tissue or fluid to be probed or operating on; a hollowcollection channel disposed along the probe body and operatively coupledto a suction tool to receive as input at least some of the tissue orfluid probed or operated on; and a monolithically fabricatedmultifunctional probe tip structure fabricated of light-transmissivematerial and integrally formed to optically engage the illuminationwaveguide to optically relay the output optical illumination from theillumination waveguide, and having formed therein a hollow probe tipchannel formed to mechanically engage the hollow collection channel tocollect at least some of the tissue or fluid probed or operated on.

In one embodiment, the output optical illumination comprises laserablation illumination.

In one embodiment, the medical probe further comprises a laser lightsource optically coupling into the illumination waveguide.

In one embodiment, the medical probe further comprises the suction tool.

Other aspects, features and/or advantages will become more apparent uponreading the following non-restrictive description of specificembodiments thereof, given by way of example only with reference to theaccompanying drawings.

BRIEF DESCRIPTION OF THE FIGURES

Several embodiments of the present disclosure will be provided, by wayof examples only, with reference to the appended drawings, wherein:

FIG. 1 is a diagram illustrating a perspective view of a medicalnavigation system, comprising a patient reference device, in anenvironmental context, such as an operation room, in accordance with anembodiment of the present disclosure;

FIG. 2 is a schematic diagram illustrating a medical navigation system,comprising a patient reference device, in accordance with an embodimentof the present disclosure;

FIG. 3 is a block diagram illustrating relationships between componentsof a surgical navigation system, such as a control and processing unit,a tracking system, a data storage device for the tracking system, systemdevices, and medical instruments/tools, in accordance with an embodimentof the present disclosure;

FIG. 4 is a diagram illustrating an access port-based surgical procedurebeing conducted by way of a navigation system, in accordance with oneembodiment of the present disclosure;

FIG. 5 is a diagram of an access port into a human brain, for providingaccess to interior brain tissue during a medical procedure, inaccordance with one embodiment of the present disclosure;

FIG. 6 is schematic side view of a multi-channel micro-optical probe,for instance a Raman spectroscopy probe having a multi-channelmicro-optical probe tip, in accordance with one embodiment of thepresent disclosure;

FIG. 6A is a schematic cross-sectional view of the probe of FIG. 6 takenalong line A-A;

FIG. 6B is a schematic cross-sectional view of the micro-optical probetip portion of the probe of FIG. 6, showing an optical interface betweenexcitation and collection fibers thereof, and the multi-channelmicro-optical probe tip;

FIG. 7 is a schematic diagram of the probe of FIG. 6 when used inconjunction with a tracked surgical tool, such as a tracked suction tooltracked via a medical navigation system, in accordance with anembodiment of the present disclosure;

FIGS. 8A to 8C are respective schematic cross-sectional diagrams ofalternative optical couplings within a multi-channel micro-optical probetip, in accordance with different embodiments of the present disclosure;

FIG. 9 is a schematic cross-sectional diagram of a multichannelmicro-optical probe tip incorporating respective channel-specificwavelength-selective features, in accordance with one embodiment of thepresent disclosure;

FIG. 10 is a schematic cross-sectional diagram of a multichannelmicro-optical probe tip incorporating a channel-specificwavelength-selective feature and respective channel-specific beamshaping features, in accordance with one embodiment of the presentdisclosure;

FIG. 11 is a schematic cross-sectional diagram of a multichannelmicro-optical probe tip incorporating both beam shaping and beamsteering features, in accordance with one embodiment of the presentdisclosure;

FIG. 12 is a schematic side view of a multifunctional probe tip regioncooperatively incorporating a multifunctional micro-optical probe tip,in accordance with one embodiment of the present disclosure;

FIG. 13 is a schematic diagram of a system that includes a flexible highresolution endoscope, in accordance with one embodiment of the presentdisclosure;

FIG. 14 is a perspective diagram of an optical element of the flexiblehigh resolution endoscope of FIG. 13, in accordance with one embodimentof the present disclosure; and

FIG. 15 is a perspective diagram of an alternative optical element thatcan be used with the flexible high resolution endoscope of FIG. 13, inaccordance with one embodiment of the present disclosure.

Elements in the several figures are illustrated for simplicity andclarity and have not necessarily been drawn to scale. For example, thedimensions of some of the elements in the figures may be emphasizedrelative to other elements for facilitating understanding of the variouspresently disclosed embodiments. Also, common, but well-understoodelements that are useful or necessary in commercially feasibleembodiment are often not depicted in order to facilitate a lessobstructed view of these various embodiments of the present disclosure.

DETAILED DESCRIPTION

Various implementations and aspects of the specification will bedescribed with reference to details discussed below. The followingdescription and drawings are illustrative of the specification and arenot to be construed as limiting the specification. Numerous specificdetails are described to provide a thorough understanding of variousimplementations of the present specification. However, in certaininstances, well-known or conventional details are not described in orderto provide a concise discussion of implementations of the presentspecification.

The probes, tools, instruments, systems and methods described herein maybe useful in the field of neurosurgery, including oncological care,neurodegenerative disease, stroke, brain trauma and orthopedic surgery;however persons of skill will appreciate the ability to extend theseconcepts to other conditions or fields of medicine. It should be notedthat the surgical process is applicable to surgical procedures forbrain, spine, knee and any other suitable region of the body.

Various apparatuses and processes will be described below to provideexamples of implementations of the system disclosed herein. Noimplementation described below limits any claimed implementation and anyclaimed implementations may cover processes or apparatuses that differfrom those described below. The claimed implementations are not limitedto apparatuses or processes having all of the features of any oneapparatus or process described below or to features common to multipleor all of the apparatuses or processes described below. It is possiblethat an apparatus or process described below is not an implementation ofany claimed subject matter.

Furthermore, numerous specific details are set forth in order to providea thorough understanding of the implementations described herein.However, it will be understood by those skilled in the relevant artsthat the implementations described herein may be practiced without thesespecific details. In other instances, well-known methods, procedures andcomponents have not been described in detail so as not to obscure theimplementations described herein.

In this specification, elements may be described as “configured to”perform one or more functions or “configured for” such functions. Ingeneral, an element that is configured to perform or configured forperforming a function is enabled to perform the function, or is suitablefor performing the function, or is adapted to perform the function, oris operable to perform the function, or is otherwise capable ofperforming the function.

It is understood that for the purpose of this specification, language of“at least one of X, Y, and Z” and “one or more of X, Y and Z” may beconstrued as X only, Y only, Z only, or any combination of two or moreitems X, Y, and Z (e.g., XYZ, XY, YZ, ZZ, and the like). Similar logicmay be applied for two or more items in any occurrence of “at least one. . . ” and “one or more . . . ” language.

The embodiments described herein provide different examples of amicro-optical surgical probes and micro-optical probe tips and methodsof manufacture therefor that address some of the limitations andimpediments of current solutions. For example, in some embodiments,micro-optical probe tips are described for assembly with, or directmanufacture onto distinct waveguides and/or optical tip sensor(s) so toimplement spectroscopic and/or multi-channel optical probes amenable foruse in a surgical context by virtue of their limited footprint (i.e.millimeter-scale diameter), a characteristic heretofore unavailableusing conventional optical manufacturing techniques and thus animpediment to the manufacture, assembly and provision of suchmicro-optical tools.

For example, in some embodiments, a micro-optical probe tip ismanufactured using a 3D printing process (e.g. 3D laser printing orwriting) whereby a respective interface for each of the optical probewaveguide, and/or respective optical paths therefor, may be integrallydesigned and manufactured within the 3D printed tip to promote enhancedoptical efficiency and accuracy without unduly impacting an overalloperative probe footprint, i.e. probe diameter. Accordingly, in someembodiments, each optical channel path through the common optical probetip structure can be uniquely and specifically defined to optimize themicro geometry respectively applicable thereto, while optionally furthertuning (wavelength specific beam shaping and/or steering, filtering,multiplexing, etc.) each optical path according to particular opticalchannel requirements or preferences.

In some embodiments, the 3D printed tip may be directly manufacturedatop respective optical probe waveguides to enhance optical probe-tipengagement and alignment while also optionally introducing complementarychannel-specific beam steering, beam shaping and/or wavelength selectivefeatures within the probe tip design and/or at a probe tip/waveguideinterface. In other embodiments, the probe tip may be manufactured tomanifest channel-specific and/or probe/tip interface characteristics tofacilitate probe and channel alignment and interfacing with the probetip upon assembly. Again, such integrated interfacing features mayinclude, but are not limited to, one or more probe-wide and/orchannel-specific beam shaping, beam steering and/or wavelength selectivefeatures, as will be detailed further below with reference to theillustrated non-limiting examples provided herewith. In the context ofpost-fabrication assembly, integrated probe tip design features may, insome embodiments, provide for robust assembly and high-efficiency matingwith corresponding channel waveguides, such as with respective fiberoptic channels, which may include, but are not limited to, one orillumination waveguides to output optical (e.g. wide spectrum and/orwavelength specific) illumination toward the tissue to be probed; one ormore collection waveguides to collect an optical response of the tissueto the output optical illumination; and other output illumination and/orinput collection waveguides that may, alone or in combination, achieve adesired or intended optical probe characteristic. In yet other examples,the micro-optical tip structure may also, or alternatively, bemanufactured atop or assembled to directly optically couple to amultichannel sensor, for example, whereby respective collection channeloptical paths (e.g. different spectral or imaging channels) are directlyoptically coupled to corresponding channel sensors or channels in aunitary multichannel sensor. Likewise, a unitary micro-optical probe tipstructure may commonly interface with a collection sensorchip-at-the-tip and an illumination waveguide to concurrently andintegrally provide multichannel (in/out) functionality. These and otherexamples will be described in greater detail below.

With reference to FIG. 6, a medical probe 800 having a micro-optical tip802 will now be described, in accordance with one embodiment. In thisembodiment, the medical probe 800 is generally adapted for internallyprobing tissue or fluid within a body, such as human body, for example,within the context of a surgical procedure (e.g. port-based or lumenbased surgical procedure). In the illustrated configuration, the probe800 comprises an elongate (flexible, rigid or semi-rigid, and optionallydisposable or exchangeable) probe body 804 having an external end 806,and an insertable end 808 to be inserted within the body toward thetissue to be probed, in this case, terminated by micro-optical probe tip802.

As noted above, and with added reference to FIGS. 6A and 6B, the probe800 consists of a multi-channel optical probe comprising one or moreillumination waveguides (e.g. optical fibers) 810 disposed along theprobe body 804 to output optical illumination via the probe tip 802, andone or more collection waveguides (e.g. optical fibers or fiber bundles)812 also disposed along the body 804 to collect, again via the probe tip802, an optical response of the tissue to the output opticalillumination. Generally, the illumination waveguide(s) 810 is opticallycoupled to a light source 814 (see FIG. 6B), such as a generalillumination (e.g. wide spectrum) light source or a wavelength-specificexcitation (e.g. laser) light source appropriate for the intendedoptical probe application. Similarly, the collection waveguide(s) 812will be optically coupled to one or more respective or joint detectors,sensors and/or optical processing systems 816 (see FIG. 6B) configuredto detect and process captured light to render intended results (e.g.optical and/or spectroscopic imaging, characterization and/ordiagnostics, etc.). Jointly, and in accordance with some embodiments,the probe 800 may ultimately provide for spectroscopic tissue probing,for example, Raman spectroscopy, whereby an excitation wavelength orwide spectrum probe provided via the illumination waveguide(s) 810 andprobe tip 802 triggers an optical response in the probed tissuemanifested by a distinct response wavelength and/or spectral profilethat can be specifically captured and relayed via the probe tip 802 andcollection waveguide(s) 812 for detection and downstream processing,whereby characteristics of the collected light (e.g. absolute orrelative amplitude, wavelength, spectral distribution, etc.) providesinterpretable information on the probed tissue (e.g. healthy vs.unhealthy tissue, tissue type, tissue damage, etc.).

In some embodiments, the probe 800 may also or alternatively provide fortissue probing using multi-spectral imaging in which a light sourceilluminates the tissue from the illumination waveguide (e.g. corewaveguide 810) while each of the other waveguides 812 collects arespective wavelength/spectrum (i.e. colour) backscattered from thesample.

In yet other embodiments, the probe 800 may further or alternativelyprovide for tissue probing using fluorescence from the tissue in whichone or more probe waveguides illuminate and excite the tissue togenerate fluorescence, while one or more other waveguides collect thefluorescence signals.

Other optical tissue characterizations may also readily apply within thepresent context without departing from the general scope and nature ofthe present disclosure, as will be understood by the skilled artisan.

In some embodiments, the probe tip 802 will consist of an opticalstructure integrally fabricated atop the illumination and collectionwaveguides 810, 812 so to provide and accurately control channelspecific interfaces therebetween. For instance, the probe tip 802 may beintegrally fabricated, e.g. via a micro-optical 3D printing process orthe like (e.g. two-photon laser writing process), as detailed below,directly atop both the illumination waveguide(s) 810 and the collectionwaveguide(s) 812 to optically relay the output optical illumination fromthe illumination waveguide(s) 810 and the optical response to thecollection waveguide(s) 812. In other embodiments, the probe tip 802 maybe separately manufactured, again for example via a micro 3D printingprocess, for precise alignment and interfacing with respective probewaveguides. These and other examples will be considered in furtherdetail below with reference to further non-limiting examples.

With particular reference to FIG. 6B, the probe tip 802 may comprise oneor more beam-shaping structures, integrally formed of sub-structures802A, B, and C monolithically joined within circumscribing shell 803 inthis example, to provide a complex optical structure amenable to relayeach optical channel to and from respective waveguides while providingprobe-specific and/or channel-specific beam shaping and/or beam steeringfeatures/elements, and/or again channel-specific wavelength selectivefeatures as will be described in greater detail below with reference tofurther exemplary embodiments. For instance, by monolithicallyfabricating complex probe tip structure 802 within circumscribing shell803, each subcomponent will benefit from inherent axial and lateralalignment (reduce or minimize tilting), while also providing internalprotection for the various refractive surfaces defined internallytherein while also inherently defining various holes/apertures/cavitiestherein for use in the subsequent deposition or layering of variouscoatings, such as channel-specific optical filters and/or wavelengthselective coatings, anti-reflective and/or reflective coatings, and thelike. For simplicity, the graphical representation of probe tip 802 willbe graphically reproduced across multiple embodiments for illustrativepurposes, only, with the understanding that different, additional and/oralternative probe tip structures, features and subcomponents may also oralternatively be considered depending on its intended purpose given aparticular multi-channel configuration and waveguide interface.

In the configuration shown in FIG. 6A, the illumination waveguide(s) 810consists of a single optical fiber that is optically coupled at one endto a light source (e.g. laser light source in the context of a Ramanprobe), whereas the collection waveguide(s) 812 consist of a set ofoptical fibers laid out in parallel to the illumination fiber 810 andarranged to circumscribe the illumination fiber 810 (e.g. forming aseven-fiber bundle). Each fiber may include a respectivesheathing/cladding to enhance optical channel isolation and minimizecross-talk, or again, be embedded or contained within a fiber bundlemedium to provide a like effect. Other fiber arrangements andconfiguration may equally be applicable, as will be appreciated by theskilled artisan. For instance, distinct single channel fibers may beused for illumination and collection purposes, whereas other embodimentsmay employ two or more such fibers for each or either of illuminationand collection. Furthermore, while illustrated fibers are schematicallyshown to form part of an assembled bundle, separate fibers may also beconsidered in an unbundled format. Also, while optical fibers areillustrated in this embodiment, other waveguide structures andcross-sections may also be considered depending on the intended opticalapplication at hand and desired result.

In the illustrated embodiment of FIGS. 6, 6A and 6B, the circumferentialcollection fibers 812 are precisely aligned to integrally andpredominantly interface with circumferential optical (e.g.circumferential beam shaping, beam steering and/or wavelength-specificor selective) features of the probe tip 802, whereas the coreillumination fiber 810 is precisely aligned to integrally andpredominantly interface with core optical (e.g. circumferential beamshaping, beam steering and/or wavelength-specific or selective) featuresof the probe tip 802, jointly forming a multi-channel (i.e.input/output) probe-tissue interface.

With particular reference to FIG. 6, the probe 800 in this embodimentcomprises a disposable or exchangeable probe section 818 whereby thedisposable probe body 804 and tip 802 are detachably coupled, e.g. viascrew-on or pressure-fitting coupler 820) to reusable probe hardware822, which for example, may reproducibly interface with probe bodyoptics to relay illumination light from a reusable light (e.g. laserand/or wide spectrum) source and collected light to one or morecorresponding detectors and/or optical processing hardware (e.g.spectrometer, optical detector, camera, imaging hardware, etc.). Giventhe 3D manufacturing process invoked, in some embodiments, to producethe probe tip 802, and the relative affordability of probe bodywave-guiding optics, disposable probes may be more readily manufacturedirrespective of probe tip optic complexity, as compared to usingotherwise costly off the shelf probe tip optics, which, in general, areprohibitively large and/or limited for multi-channel applicability andcomplexity.

In one embodiment, the multi-channel optical probe 800 may be used as astand-alone device whereby probing functions may be performed alone orin combination with other complementary functions (not shown), forexample, in a surgical context in obtaining optical imaging,characterization and/or diagnostic information from probed tissue. Asfurther detailed herein, the probe may be dynamically tracked ormonitored via a corresponding surgical navigation system, monitored viaone or more optical or surgical tracking tools, or again manuallyoperated and/or tracked via appropriate direct or magnified surgicalvisualization tools, for example. Likewise, probe outputs may beprocessed and/or monitored in various forms to provide desired results,such as via graphical or raw data outputs, imaging overlays, indexationand/or annotation, graphical readouts, and the like. These and othersuch examples will be readily appreciated by the skilled artisan uponreference to the disclosure as a whole.

With added reference to FIG. 7, the probe 800 may also or otherwise beoperated in cooperation with one or more complementary tools orinstruments 900, for example, where certain complementary features orfunctions may be leveraged by this tool 900 to avoid hardwareduplication and/or reduce an invasive impact of the procedure takingplace. In the illustrated example, the complementary tool 900 includes adisposable tool body 904 and tip 902 detachably coupled via screw orpressure-fitting coupler 920 to reusable hardware, in this casecomprising an onboard controller 922 (e.g. onboard power source,wireless communication transceiver, operational firmware, drivers,etc.), tracking markers 924 and a tethered link 926 (e.g. suction orresection tool output, wired communication line, power line, etc.). Forexample, the complementary tool 900 may consist of a tracked suction,imaging and/or resection tool that can work cooperatively with theoptical probe 800. For example, the probe 800 may leverage the tool'strackability to provide relative tracking of the optical probe tip 802and tissue thus probed. Conversely, optical characterization of theoptically probed tissue may be used to locate surgical areas or tissueof interest that, once identified, may be immediately removed, forexample, via a complementary resection tool 900. Complementary imagingand/or suction functions may equally apply, as will be readilyappreciated by the skilled artisan.

With reference to FIGS. 8A to 8C, different illustrative configurationsand arrangements for micro-optical tip 802 are provided, in accordancewith different embodiments, as they each interface with distinctillumination and collection waveguides 810 and 812, respectively. Asnoted above, each of these configurations may be manufactured directlyatop channel waveguides, or again manufactured for precisionpost-fabrication assembly and optical coupling thereto.

In FIG. 8A, the micro-optical probe tip 802 is manufactured to includerespective channel ports 830 to receive corresponding channel waveguidestherein for mating and precise optical engagement therewith. In doingso, a respective distance between a channel waveguide output and probetip beam shaping and/or beam steering features can be preciselycontrolled for optimal performance, and in some embodiments, discretelymanufactured to provide distinct channel-specific distances,configurations and/or interfaces.

In comparison, the micro-optical probe tip 802 of FIG. 8B ismanufactured to include a common port interface 832, whereby a commonport depth and interface for all channels may be precisely defined.

In yet another example, as shown schematically in FIG. 8C, respectivewaveguide channel interfaces may be discretely manufactured as effectivechannel waveguide extensions 834 so to precisely control beam shapingand/or beam steering at the interface, for instance, via common orrespective waveguide extension lengths, profiles and/or properties.

FIG. 9 provides yet another example of a micro-optical probe tip 802, inthis embodiment, encompassing one or more wavelength-selective featuresintegrated therein to further govern optical properties at the probe tipinterface with channel waveguides 810, 812. For example, the probe tip802 shown in FIG. 9 includes respective waveguide channel ports 830 asillustrated in FIG. 8A, but also incudes respective optical filterlayers/coatings 836, 838 nested therein, whereby an illuminationwavelength output from the illumination waveguide 810 may be preciselyselected and controlled by an illumination wavelength-selecting filter836 (e.g. excitation wavelength in a Raman probe), whereas a collectionwavelength input into the collection waveguides 812 may be preciselyselected and controlled by a collection wavelength-selecting filter 838(e.g. collection wavelength in a Raman probe offset from the excitationwavelength).

Similarly, the micro-optical probe tip 802 of FIG. 10 also includescollection waveguide filters 838, but rather contemplates an embodimentwhere an illumination wavelength needs not be equally filtered (e.g.within the context of a wavelength specific illumination source such asa laser light source having a sufficiently narrow bandwidth, whereas anoffset collection wavelength is still filtered to filter out sourcewavelength reflections). In the embodiment of FIG. 10, the probe tip 802reprises the waveguide extensions 834 of FIG. 8C, while embeddingcollection waveguide filters 838 therewith and providing for distinctlyseparated illumination and collection beam shaping and/or steeringstructures (840, 842), nonetheless monolithically manufactured in anintegrated micro-optical tip structure. It will be appreciated that thespecific features and elements manufactured in each channel-specificmicro-optical substructures may vary depending on the application athand, be they specifically designed and manufactured to focus, diffuse,collimate, project, redirect and/or provide one or more wavelengthselective or dispersive functions (e.g. wavelength-specific filter,diffractive element such as structural grating, etc.).

With reference to FIG. 11, and in accordance with yet anotherembodiment, an alternative micro-optical probe tip 1102, in thisembodiment, structurally combining in an integrated structure not onlymulti-channel beam shaping features as illustratively described above tointerface with respective channel waveguides 810, 812, but also a commonmultichannel beam steering structure 1140 comprising, in thisembodiment, a right-angle beam steering structure having a 45-degreeinternally reflective surface 1142 (e.g. coated or total internalreflective surface) monolithically fabricated within the tip structure1102 and redirecting light to and from a peripheral window or likeaperture 1144. Accordingly, the micro-optical tip structure 1102provides, within a minimally invasive probe tip structure (e.g.millimeter scale), both multichannel beam shaping and overall opticalredirection turning an otherwise axial probe into a radial probe, whichprovides further intraoperative access to in vivo tissue probing andcharacterization not only down axis but also around a full periphery ofa given surgical access region (i.e. down port periphery in a port-basedprocedure, peripheral probing within a lumen-based procedure, etc.).

Expanding from the embodiment illustrated in FIG. 11, FIG. 12 provides adiagrammatical view of a combined multifunctional probe 1200, in thisembodiment combining a resection tool 1250, a multichannel (e.g.spectroscopic probe) optical probe 1260 as described above comprisingillumination and collection waveguides interfacing with correspondingbeam-shaping and/or steering probe tip features (not shown) foroptically operating via peripheral window/aperture 1262, and a generalimaging probe 1270, for example, providing visible imaging of thesurgical site (e.g. relaying images back to an external monitor orscope) via visible imaging window/aperture 1272. Using the micro-opticalprobe tip manufacturing and interfacing techniques described above, amultifunctional tool, optionally integrated within a singular tool butalternatively commonly addressable via a common tool-probealignment/attachment such as illustrated for example at FIG. 7, may beused to provide enhanced intra-surgical functions while minimizing toolinvasiveness, i.e. by minimizing an overall tool diameter andoperational volume requirements.

For example, within the context of an ablation or like tool, anintegrated multi-functional micro-fabricated tool tip structure may usedto combine an optical output feature shaped and configured to output adesired optical ablation output, with an ablation product collectioninput for example, operatively coupled to an integrated or cooperativelycoupled suction tool. For example, the probe tip optical element can beshaped and configured to interface with an ablation laser source andprobe body fiber to shape and direct laser irradiation (e.g. opticalbeam shaping and/or redirection features, etc.) toward an intra-surgicaltarget. The same micro-fabricated probe tip may also have integrally(e.g. monolithically) fabricated therein one or more hollow tipcollection channels (e.g. hollow tube or cylindrical features) shapedand configured to interface with one or more corresponding hollowcollection channels (e.g. fibers) disposed along the probe's elongatebody, for example, through which suction can be applied from acorresponding suction tool. Accordingly, the micro-fabricated probe tipmay include not only optical features (beam shaping, redirectingfeatures and/or wavelength selective features), but also structurefeatures such as holes, cavities and/or channels to concurrentlyinterface with corresponding probe tools to deliver multifunctionalfeatures such as suction, resection, ablation or the like.

With reference now to FIG. 13, and in accordance with yet anotherembodiment, a schematic diagram is provided of a system 600 thatincludes an example of a flexible high resolution endoscope 601 that mayemploy the techniques described herein. It is appreciated that elementsof system 600 are not drawn to scale, but are depicted schematically toshow functionality.

Endoscope 601 generally comprises: a plurality of optical fibers orfiber bundles 603; a plurality of lenses 605 each integrally formed in acommon optical element 613 located at common distal end 609 of theendoscope 601; and, a plurality of cameras 607 at a proximal end 611 ofthe endoscope 601. In the illustrated embodiment, the lens 605 andcameras 607 are associated in a one-to-one relationship with theplurality of optical fibers/bundles 603, thus allowing each lens 605 torelay light captured thereby toward a corresponding camera 607 via adedicated intermediary fiber/bundle 603. As above, the common opticalelement 613 can be manufactured of a 3D printing or like process so tointegrally encompass each constituent lens 605 in efficient manner whilealso encompassing optical/structural features to optimize an alignmentof each lens 605 with its corresponding fiber/bundle 603. Likewise, thecommon optical element 613 may be effectively manufactured directly atopthese fibers/bundles 603 to integrally secure proper alignment andoptical coupling, while also optionally providing for additional beamforming, steering and/or wavelength specificity.

In general, endoscope 601 is configured to acquire a plurality of imagesof a tissue sample 620, which can include, but is not limited to, atissue sample accessible via access port 12 (described below). Inparticular, respective distal ends 609 of the plurality of opticalfibers/bundles 603, and respective lenses 605 located at respectivedistal ends 609, can be spaced apart from one another to providedifferent views of objects (such as tissue sample 620) in front of therespective distal ends 609. In some of these implementations endoscope601 can thereby form a plenoptic camera.

It will be appreciated that endoscope 601 is not limited to four camera,lens and fiber assemblies, but can rather comprise as few as two suchassemblies, and can comprise more than four such assemblies, in eachconfiguration allowing for the optional formation of a three-dimensionalcamera.

As depicted, each lens 605 is integrally formed in a common opticalelement 613 located at common distal end 609. Common optical element 613can be manufactured of suitable optical (i.e. light-transmissive)materials, such as those described above as being amenable for 3Dprinting and manufacturing purposes.

In doing so, the manufactured lens 605 may exhibit different depths offield, different fields of view of objects in front of the plurality oflenses 605, and/or different angular view of objects in front of theplurality of lenses 605, as may be required to achieve a desired effect.Hence, when endoscope 601 is imaging tissue sample 620, tissue sample620 can be imaged using at least two different depths of field and/or atleast two different fields of view and/or at least two different angularviews, for example.

Each camera 607 can include, but is not limited to one or more of acharge-coupled device (CCD) camera, a digital camera, an optical camera,and the like, and is generally configured to acquire digital images, andin particular digital images received from a respective lens 605 via arespective optical fiber bundle 603. While not depicted, each camera 607can further include one or more respective lenses for focusing lightfrom a respective optical fiber 603 onto a respective imaging element(such as a CCD). While not depicted, endoscope 601 can include one ormore devices for coupling optical fiber bundles/fibers 603 to arespective camera 607.

Controller 615 can comprise any suitable combination of computingdevices, processors, memory devices and the like. In particular,controller 615 can comprise one or more of a data acquisition unit,configured to acquire data and/or images at least from cameras 607, andan image processing unit, configured to process data and/or images fromcameras 607 for rendering at display device 626. Hence, controller 615is interconnected with cameras 607 and display device 626. In someimplementations, controller 615 can comprise control and processing unit300 depicted in FIG. 3, and/or controller 615 can be in communicationwith control and processing unit 300 depicted in FIG. 3 and/orcontroller 615 can be under control of communication with control andprocessing unit 300 depicted in FIG. 3.

In some implementations, however, controller 615 can be a component ofendoscope 601 such that endoscope 601 comprises controller 615. In theseimplementations, endoscope 601 can be provided as a unit with controller615 which can be interfaced with control and processing unit 300depicted in FIG. 3, and the like.

Display device 626 can comprise any suitable display device including,but not limited to, cathode ray tubes, flat panel displays, and thelike. For example, display device 626 can comprise one or more ofmonitors 205, 211, as depicted in FIG. 2, and/or displays 305, 311depicted in FIG. 3.

Further details as to an implementation of the device of FIG. 13, anddata captured thereby, can be found in co-pending PCT Application No.PCT/IB2016/054931, the entire contents of which are hereby incorporatedherein by reference.

In some embodiments, one or more sensor chips can be provided at the tipof an endoscope (i.e. chip-on-the-tip endoscope) in which electricalcables connect from the distal end of the endoscope to the proximal endto the endoscope controller rather than to relay optical signals theretovia a set of optical fibers/waveguides. For instance, a micro-opticalstructure as described above could be fabricated directly atop, or todirectly interface with the one or more tip sensor chip(s) rather thanto optically couple into corresponding waveguides. This approach mayimprove endoscope robustness by eliminating intermediating waveguidesthat can get broken from wear and tear while also reducing theendoscope's overall size. Using the probe tip optic design andmanufacturing processes described herein, the typically reduced opticalquality expected form such design (e.g. distortion, aberration, opticalresolution, and stray light) may be circumvented or at least attenuatedby providing enhanced tip optics for such chip-on-the-tipimplementations. In fact, the same micro-optical tip structure may bedesigned to improve endoscopic imaging quality while also improvingillumination by focusing light relayed by illumination waveguidessurrounding the sensor chip.

In some embodiments, a non-symmetrical lens can be designed on a givenfiber bundle tip and/or the sensor chip at the tip of the endoscope tooptimize imaging angle and spacing for 3D endoscope imaging, forexample.

With reference to FIG. 14, common optical element 613 is generallyconfigured to both provide lenses 605 and couple together the pluralityof optical fibers/bundles 603 at common distal end 609. Hence, commonoptical element 613 comprises lenses 605 and, as depicted, respectiveslots 901 for receiving a respective optical fiber/bundle 603 on aproximal side, each slot 901 in a body of common optical element 613,and each slot 901 terminating at a respective lens 605 at distal end609. Hence, each slot 901 has a diameter that is similar to a diameterof a respective optical fiber bundle 603 such that each slot 901 canreceive a respective optical fiber bundle 603 and seat a distal end ofeach respective optical fiber bundle 603 at a respective lens 605.

While not depicted, common optical element 613 can further comprise amechanism for fixing each respective optical fiber/bundle 603 within arespective slot 901; alternatively, adhesives (including, but notlimited to optical adhesives) can be used to fix a respective opticalfiber bundle 603 within a respective slot 901. In yet anotheralternative, the common optical element 613 may be directly manufacturedatop fibers/bundles 603 in providing direct optical engagementtherewith.

Attention is next directed to FIG. 10 which depicts an alternativecommon optical element 613 a, which is substantially similar to opticalelement 613, with like elements having like numbers, however with an “a”appended thereto. Hence, optical element 613 a comprises a plurality oflenses 605 a at a distal end 609 a. However, in contrast to opticalelement 613, optical element 613 a comprises eight lenses 605 a, and oneslot 901 a configured to receive a plurality of optical fibers/bundles.However, optical element 613 a can comprise fewer than eight lenses 605a and more than eight lenses 605 a.

Hence, provided herein is a flexible endoscope that comprises multipleoptical fibres/bundles, each coupled to an integrated (e.g.monolithically fabricated) multi-lens array at a distal end and multiplecameras at a proximal end. Each lens on the array can convey a separateimage to the distal end of each optical fibre bundle and cameras coupledto the proximal end of the optical fibre bundles acquire separatepixelated images. These lower resolution images, acquired by each of thecameras, can be merged and/or combined, and reconstructed usingprinciples of light field imaging and processing, to produce asuper-resolution image. This can allow for much higher resolutionimaging than with conventional endoscopes, which can allow for betterdiagnosis and treatment.

Furthermore, using light field processing of the separate images fromthe cameras, a depth-map of objects imaged by the lenses can bereconstructed, which can allow structures with differing depth to bemore easily detected and/or seen. By taking advantage of the underlyingoptics of the method, omnifocusing (having all object in the scenein-focus), selective post-acquisition focusing, and depth of fieldcontrol is possible post-acquisition and real-time. This post-processingcan allow for removal of “dead” pixels which can be caused by brokenfibres within fiber bundles without significant loss of detail

As noted above, different manufacturing processes may be invoked tomonolithically construct a micro-optical probe tip structure amenable tointerfacing with, or being fabricated directly atop or upon, a set ofmultichannel waveguides, such as illumination and/or collectionwaveguides, for example, in an in vivo tissue imaging, characterizationand/or diagnostic probe, such as an endoscopic and/or spectroscopicprobe to name a few examples.

In some embodiments, a 3D laser printing process (interchangeablyreferred to as a laser writing process or again an additive lasermanufacturing process) is invoked to process and progressively fabricatethe probe tip structure using transparent materials. For example, one 3Dlaser printing option includes, but is not limited to, a multiphotonlithography process (see for example, Gissibl et al., Two-photon directlaser writing of ultracompact multi-lens objectives, Nature Photonics10, 554-560 (2016); Gissibl et al., Sub-micrometer accurate free-formoptics by three-dimensional printing on single-mode fibres, NatureCommunications 7, Article number: 11763 (2016); Thiele et al.,Ultra-compact on-chip LED collimation optics by 3D femtosecond directlaser writing, Optics Letters, Vol. 41, No. 13, July 2016, the entirecontents of each of which are hereby incorporated herein by reference)in which femtosecond laser pulses can be used to trigger two-photonabsorption in highly transparent photoresists to additively realize themonolithic additive fabrication of a micro-optical probe tip design froma single material (e.g. high optical quality photoresist such as IP-S,Nanoscribe GmbH), which may, in some examples, ultimately encompassoptical elements at the micro and even nanometer scale.

Accordingly, micro and nano-scale features may be explicitly designedwithin a singular probe tip structure, as illustratively describedabove, to produce micro-scale optics integrating particular micro and/ornano-scale beam shaping and/or steering features that, when assembled orbuilt directly atop a set of multichannel waveguides, addressesrespective channel optical path requirements. Such designs may berealized and optimized, for example, using available optical designsoftware (e.g. ZEMAX by Zemax, LLC), and exported and converted into astereolithographic file format to execute the bi-photon lithographyusing, for example, dip-in direct laser writing using a commerciallyavailable femtosecond laser lithography system (e.g. PhotonicProfessional GT, Nanoscribe GmbH, Germany). Likewise, the introductionof interstitial coatings, layers, textures and/or structures (e.g.non-reflective coatings, reflective coatings, optical filters, gratings,etc., via atomic layer deposition (ALD), micro ornano-patterning/texturizing, etc.) upon and/or between additivelyfabricated optical features may further enhance multichannel versatilitywithout unduly increasing a form factor of the overall probe tipstructure, namely allowing to construct and maintain tip structureshaving diameters in the order of 1 or 2 mm in some embodiments, or againbelow 1 mm in some alternative embodiments, or yet again in the order of0.5 mm in some further alternative embodiments. In yet otherembodiments, complex multichannel probe tip structures may bemanufactured as described herein to accommodate multichannel bundleshaving greater diameters, such as 5 mm or even 10 mm. Ultimately, probetip form factors may be limited or impacted to some extend to the formfactors of the waveguides interfacing with the probe tip, rather than bypreviously prohibitively large probe tip form factors, for instancewhere a multichannel fiber bundle (e.g. comprising at least two (2) andas many as 4 to 20 or 25 fibers in a millimeter scale probe) may definethe ultimate probe tip form factor by virtue of a combined bundlediameter. Accordingly, even when a multichannel probe is combined withother tools in a multifunctional tool design, assembly or set, theoverall instrument form factor can be drastically reduced and managed byvirtue of the herein described techniques for providing high qualitymicro-optical probe tips.

As noted above, the solutions described herein are amenable for use indifferent medical or surgical contexts. However, for the sake ofillustration, reference will now be made to a non-limiting example of aport-based neurosurgical system and environment in which the opticalprobes described herein may be of particular use. It will nonetheless beappreciated by the skilled artisan that this environment is describedsolely to provide greater context for the embodiments described herein,and that various other surgical or medical environments and systems mayequally benefit from the features, functions and advantages provided bythe herein-described embodiments.

With reference to FIGS. 1 and 2, and in accordance with one embodiment,an exemplary port-based surgical system and associatedtracking/navigation system, incorporating for example a micro-opticalprobe as described herein, will now be described. As noted above, itwill be appreciated that the micro-optical probe described herein withinthe context of a port-based surgical system may also be amenable toother similar or alternate surgical systems and procedures, and that,without departing from the general scope and nature of the presentdisclosure. Namely, the utility and applicability of theherein-described probes and tools is not limited to port-based and/orneurological procedures, but rather, may prove particularly useful anddesirable in a number of surgical and/or medical environments.

In the illustrated example, the surgical system encompasses an exemplarysurgical navigation system 200 operable to track various patientreference devices, in an environmental context, such as an operationroom (OR). The system 200 supports, facilitates, and enhances minimallyinvasive access port-based surgery using a minimally invasive accessport-based surgical procedure, though non port-based procedures mayequally be considered herein as noted above.

By example only, a surgeon 101 conducts a minimally invasive access portbased surgery on a subject, such as a patient 102, in an OR environment.The navigation system 200 generally includes an equipment tower 201, arobotic arm 202 to support an external optical scope 204, and at leastone display or monitor 205, 211 for displaying a video image. By exampleonly, an operator 103 is also present to operate, control, and provideassistance for the system 200.

With particular reference to FIG. 2, the equipment tower 201 isgenerally mountable on a frame, e.g., a rack or a cart, and isconfigured to accommodate a power supply, e.g., an AC adapter powersupply, and at least one computer or controller operable by at least onea set of instructions, storable in relation to at least onenon-transitory memory device, corresponding to at least one of surgicalplanning software, navigation/tracking software, or robotic software formanaging at least one of the robotic arm 202 and at least oneinstrument, such as a surgical instrument, e.g., the access port 206,the introducer 210, and/or one or more other downstream (instrumented)surgical tools (not shown) used during the procedure. For example, thecomputer comprises at least one of a control unit and a processing unit,such as control and processing unit 400 or 1530 schematically shown inFIGS. 8 and 3, respectively. In the illustrated embodiment, theequipment tower 201 comprises a single tower configured to facilitatecoupling of the at least one display device. e.g., a primary displaydevice 211 and a secondary display device 205, with the at least onepiece of equipment. However, other configurations are also encompassedby the present disclosure, such as the equipment tower 201 comprisingdual towers configured to facilitate coupling of a single display, etc.The equipment tower 201 is also configurable to accommodate anuninterruptible power supply (UPS) for providing emergency power.

To maintain constant positioning of the patient's anatomy of interestduring a given procedure, the patient's anatomy may be held in place bya holder appropriate for the procedure in question. For example, in aport-based neurosurgical procedure, such as that illustrated in FIG. 2,a patient's head can be retained by a head holder 217. A craniotomy isperformed, a dura flap is formed and retracted, and the access port 206and introducer 210 can then be inserted into the patient's brain 102 b,and the planed procedure is executed while the patient's head remainseffectively immobile.

The system also includes a tracking system 213 that is generallyconfigured to track at least one instrument, such as a surgicalinstrument, tool and/or probe. In FIGS. 1 and 2, the tracking system isinitially utilized to track the access port 206 and introducer 210 whilethe access port is being introduced within the patient's brain so toultimately locate and define the surgical site and surrounding surgicalcavity. However, other intra-operative surgical tools, such as, but notlimited to, inner-cavity pointing tools, suction tools, tissue probes(e.g. Raman probes, OCT probes, spectroscopic probes, endoscopes, etc.),resection tools and the like, are also advantageously tracked, alone orin combination, by the tracking system to enhance accuracy and precisionof executed operative procedures. Instrument tracking can thussignificantly assist the surgeon 101 during the minimally invasiveaccess port-based surgical procedure (or like procedures) both inguiding and confirming procedural actions, but also in aligningreal-time surgical cavity imaging, probing and characterization, asdetailed below within the context of micro-optical surgical probes, withpre-operative imaging data and intra-operative external imaging (e.g.captured via external optical scope 204 and/or other cameras discussedbelow). Accordingly, tracking instruments/tools as noted above cansignificantly benefit enhanced or complementary inner-cavity imaging,localization, characterization and/or mapping.

Accordingly, the tracking system 213 is configured to track anddetermine, e.g., in real-time by way of a set of instructionscorresponding to tracking software and storable in relation to at leastone non-transitory memory device, the location of the one or moretracked instruments during the surgical procedure, while also generallytracking a position of the robotic arm 202.

In the illustrated embodiment, the tracking system 213 generallycomprises at least one sensor (not shown) for detecting at least onefiducial marker 212 disposable in relation the one or more OR items(e.g. surgical arm 202) and/or surgical instruments (introducer 210) tobe tracked. In one example, the tracking system 213 comprises athree-dimensional (3D) optical tracking stereo camera, such as aNorthern Digital Imaging® (NDI) optical tracking stereo camera, whichcan be configured to locate reflective sphere tracking markers 212 in 3Dspace. In another example, the tracking camera 213 may be a magneticcamera, such as a field transmitter, where receiver coils are used tolocate objects in 3D space, as is also known in the art. Accordingly,location data of the mechanical arm 202, access port 206, introducer 210and and/or other tracked instruments/tools, may be determined by thetracking camera 213 by automated detection of tracking markers 212placed on these tools, wherein the 3D position and orientation of thesetools can be effectively inferred and tracked by tracking software fromthe respective position of the tracked markers 212.

In the illustrated embodiment of FIG. 2, the secondary display 205provides an output of the tracking camera 213, which may include, but isnot limited to, axial, sagittal and/or coronal views as part of amulti-view display, for example, and/or other views as may beappropriate, such as views oriented relative to the at least one trackedinstrument (e.g. perpendicular to a tool tip, in-plane of a tool shaft,etc.). These and other views may be considered in various single ormulti-view combinations, without departing from the general scope andnature of the present disclosure.

Still referring to FIG. 2, minimally invasive brain surgery using accessports is a recent method of performing surgery on brain tumors. In orderto introduce an access port 206 into a brain, such as the patient'sbrain 102 b, of a patient head's 102 a, an introducer, e.g., theintroducer 210, comprises an atraumatic tip disposable within the accessport 206 to facilitate positioning the access port 206 within thepatient brain 102 b. As noted above, the introducer 210 furthercomprises at least one fiducial marker 212 for facilitating tracking bythe tracking system 213. Generally, tracked tools such as introducer 210will include a plurality of fiducial markers to enhance trackability in3D space.

After the introducer 210 and the access port 206 are inserted into thebrain 102 b, the introducer 210 is removed to facilitate access to thetissue of the brain 102 b through the central opening of the access port206. However, after the introducer 210 is removed, the access port 206is no longer being tracked by the tracking system 213. However, theaccess port 206 is indirectly trackable by way of additional pointingtools (not shown) configured for identification by the navigation system200.

In the illustrated embodiment of FIG. 2, the navigation system 200further comprises a guide clamp 218 for retaining the access port 206.The guide clamp 218 is configured to optionally engage and disengage theaccess port 206, eliminating the need to remove the access port 206 fromthe patient 102. In some embodiments, the access port 206 is configuredto slide up and down within the guide clamp 218 in a closed position.The guide clamp 218 further comprises a locking mechanism (not shown),the locking mechanism being attachable or integrable in relation to theguide clamp 218, and the locking mechanism being optionally manuallyactuable, e.g., using one hand as further below described.

The navigation system 200 further comprises an articulating arm 219,such as a small articulating arm, configured to couple with the guideclamp 218. The articulating arm 219 comprises up to six (6) degrees offreedom for facilitating positioning of the guide clamp 218. Thearticulating arm 219 is attachable at a location in relation to the headholder 217, or in relation to any other suitable patient supportstructure, to ensure, when locked in place, that the guide clamp 218 isfixed in relation to the patient's head 102 a. The articulating arm 219comprises an interface 219 a disposable in relation to the guide clamp218, wherein the interface 219 a is at least one of flexible or lockableinto place. Flexibility of the interface 219 a facilitates movability ofthe access port 206 into various positions within the brain 102 b, yetstill maintains rotatability about a fixed point.

The navigation system 200 may further or alternatively comprise aplurality of wide-field cameras, e.g., two additional wide-field cameras(not shown) being implemented with video overlay information, whereinone camera is mountable in relation to the optical scope 204 and theother camera is mountable in relation to the navigation system 213 (i.e.within the context of an electromagnetic tracking system). In the caseof the navigation system 213 comprising an optical tracking device, avideo image can be directly extracted therefrom. Video overlayinformation can then be used to enhance available intra-operativeinformation, for example, by providing an image displaying a physicalspace and confirming tracking system registration alignment and optionalcorresponding text and/or indicia, an image displaying a motion range ofthe robotic arm 202 holding the optical scope 204 and optionalcorresponding text and/or indicia, and/or an image displaying a guidehead positioning and a patient positioning and optional correspondingtext and/or indicia.

Other image overlays, as will be described in greater detail below, mayfurther include intraoperative cavity imaging and/or characterizationdata (e.g. colour mapping, partial image transparency overlay, textand/or indicia), such as provided by a micro-optical probe as describedherein. Using such real-time intraoperative inner cavity imaging andcharacterization data may not only enhance other intraoperative images,such as those rendered by overhead scopes and/or cameras, but alsoseamlessly integrate with pre-operative images and/or data, forinstance, acquired pre-operatively using one more imaging techniques.Accordingly, the surgeon and/or other surgical equipment operator canexecute procedures and/or actions with greater clarity, certainty andvisibility, thus leading to improved outcomes and risk reduction.

With reference to FIG. 4, a diagram of an access port-based surgicalprocedure conducted by way of the navigation system 200 is illustrated,in accordance with some embodiments of the present disclosure. In thisexample, a surgeon 501 is resecting a tumor from the brain of a patient502 through an access port 504. An external scope 505 is coupled with arobotic arm 504, and is used to view down port 504 at a sufficientmagnification to allow for enhanced visibility down port 504. The outputof external scope 505 is rendered on a visual display.

As introduced above, the procedure illustrated in FIG. 5 may involvedisposing active or passive fiduciary markers, respectively, 507, 508,e.g., spherical markers, in relation to at least one of the access port504 or the external scope 505 for facilitating their tracking (locationof these tools) by the tracking system (e.g. tracking system 213 of FIG.2). The active or passive fiduciary markers, 507, 508, are sensed bysensors of the tracking system 213, whereby identifiable points areprovided. A tracked instrument is typically indicated by sensing agrouping of active or passive fiduciary markers, 507, 508, whereby arigid body, such as a tool or probe, is identified by the trackingsystem 213, and whereby the position and orientation in 3D of a trackedinstrument, such as a tool or probe, is determinable. Namely, asubstantially rigid tool can be tracked in 3D space to effectivelylocate and orient the tool and its various segments and constituentcomponents, provided such segments/components are previously defined andstored against the tracked tool type. Accordingly, a tracked tool mayinvoke not only general tracking, but also tracking, for example, of thetool's tip or body, and any sensors or probes, as will be detailedbelow, that may be operatively coupled thereto or utilized therewith ina designated configuration (e.g. at or near a tool tip, angled relativeto a tool tip or shaft, displaced and/or angled relative to othertool-mounted sensors, etc.). Typically, a minimum of three active orpassive fiduciary markers, 507, 508, are placed on a tracked tool todefine the instrument. In the several figures included herewith, fouractive or passive fiduciary markers, 507, 508, are used to track eachtool, by example only.

In one particular example, the fiduciary markers comprise reflectospheremarkers in combination with an optical tracking system to determinespatial positioning of the surgical instruments within the operatingfield. The spatial position of automated mechanical arm(s) or roboticarm(s) used during surgery may also be tracked in a similar manner.Differentiation of the types of tools and targets and theircorresponding virtual geometrically accurate volumes can be determinedby the specific orientation of the reflectospheres relative to oneanother giving each virtual object an individual identity within thenavigation system. The individual identifiers can relay information tothe system as to the size and virtual shape of the tool within thesystem. The identifier can also provide information such as the tool'scentral point, the tools' central axis, the tool's tip, etc. The virtualtool may also be determinable from a database of tools provided to thenavigation system 200. The marker positions can be tracked relative toan object in the operating room such as the patient. Other types ofmarkers that can be used may include, but are not limited to, radiofrequency (RF), electromagnetic (EM), pulsed and un-pulsedlight-emitting diodes (LED), glass spheres, reflective stickers, uniquestructures and patterns, wherein the RF and EM would have specificsignatures for the specific tools to which they would be attached. Thereflective stickers, structures, and patterns, glass spheres, LEDs couldall be detected using optical detectors, while RF and EM could bedetected using antennas. Advantages to using EM and RF tags may includeremoval of the line of sight condition during the operation, where usingthe optical system removes the additional noise from electrical emissionand detection systems.

In a further embodiment, printed or 3D design markers can be used fordetection by an auxiliary camera and/or external scope. The printedmarkers can also be used as a calibration pattern to provide distanceinformation (3D) to the optical detector. These identification markersmay include designs such as concentric circles with different ringspacing, and/or different types of bar codes. Furthermore, in additionto using markers, the contours of known objects (e.g., side of the port,top ring of the port, shaft of pointer tool, etc.) can be maderecognizable by the optical imaging devices through the tracking system213. Similarly, or in addition thereto, structural information relatingto each tool (size, dimensions, distance and geometric orientationrelative to markers) may be used to extrapolate the position andorientation various tool segments, such as the tool tip, and varioussensors that may be operatively mounted thereon or associated therewith,as noted above.

As will be appreciated by the skilled artisan, while the above lists anumber of tracking techniques and related marker types, other known andfuture techniques may also be considered within the present context tosupport and enhance operation of the tracked surgical tools, i.e.optical probes and associated tools, described herein. Namely, thetracking technique for each instrument will generally allow for thetracking of the instrument's position and orientation within a givenframe of reference, in which the position and orientation can betracked, relayed and/or rendered on the surgical system's one or moredisplays to visually locate the tool, or data/images acquired thereby,within the context of the procedure taking place and/or any otherwiseavailable pre-operative and/or intraoperative images/details.

FIG. 5 illustrates the insertion of an access port 12 into a human brain10, in order to provide access to interior brain tissue during a medicalprocedure. In FIG. 5, access port 12 is inserted into a human brain 10,providing access to interior brain tissue. Access port 12 may include,but is not limited to, instruments such as catheters, surgical probes,and/or cylindrical ports such as the NICO BrainPath. Surgical tools andinstruments may then be inserted within a lumen of the access port 12 inorder to perform surgical, diagnostic or therapeutic procedures, such asresecting tumors as necessary. However, the present specificationapplies equally well to catheters, DBS needles, a biopsy procedure, andalso to biopsies and/or catheters in other medical procedures performedon other parts of the body.

With reference to FIG. 3, and in accordance with one embodiment,relationships between components of an overall surgical navigationsystem 200, such as a control and processing unit 300, a tracking system321, a data storage device 342 for the tracking system 321, and systemdevices 320, and medical instruments 360, will now be described. Thecontrol and processing unit 300 comprises at least one processor 302, amemory 304, such as a non-transitory memory device, a system bus 306, atleast one input/output interface 308, a communications interface 310,and storage device 312. The control and processing unit 300 isinterfaced with other external devices, such as the tracking system 321,data storage 342 for the tracking system 321, and external user inputand output devices 344, optionally comprising, for example, at least oneof a display device, a keyboard, a mouse, a foot pedal, a microphone,and a speaker.

The data storage 342 comprises any suitable data storage device, such asa local or remote computing device, e.g. a computer, hard drive, digitalmedia device, or server, having a database stored thereon. The datastorage device 342 includes identification data 350 for identifying atleast one medical instrument 360 and configuration data 352 forassociating customized configuration parameters with at least onemedical instrument 360. The data storage device 342 further comprises atleast one of preoperative image data 354 and medical procedure planningdata 356. Although data storage device 342 is shown as a single device,understood is that, in other embodiments, the data storage device 342comprises multiple storage devices. The data storage device 342 is alsoconfigured to store data in a custom data structure corresponding tovarious 3D volumes at different resolutions, wherein each may becaptured with a unique time-stamp and/or quality metric. This customdata structure provides the system 200 (FIGS. 1 and 2) with an abilityto move through contrast, scale, and time during the surgical procedure.

Medical instruments (tools) 360 are identifiable by the control andprocessing unit 300, wherein the medical instruments 360 are coupledwith, and controlled by, the control and processing unit 300.Alternatively, the medical instruments 360 are operable or otherwiseindependently employable without the control and processing unit 300.The tracking system 321 may be employed to track at least one of themedical instruments 360 and spatially register the at least one medicalinstrument 430 in relation to an intra-operative reference frame. Asnoted above, the tracking system 321 may thus furnish the requisiteposition, orientation and location data to associate tool/probe datawith corresponding locations within the surgical cavity.

The control and processing unit 300 is also interfaceable with a numberof configurable devices, and may intra-operatively reconfigure at leastone such device based on configuration parameters obtained fromconfiguration data 352. Examples of devices 320 include, but are notlimited to, at least one external imaging device 322, at least oneillumination device 324, robotic arm 305, at least one projection device328, and at least one display device 311, 305.

The control and processing unit 300 is operable by the at least oneprocessor 302 and the at least one memory 304. For example, thefunctionalities described herein are at least partially implemented viahardware logic in processor 302 by way of the instructions stored inmemory 304 though at least one processing engine 370. Examples ofprocessing engines 370 include, but are not limited to, user interfaceengine 372, tracking engine 374, motor controller 376, image processingengine 378, image registration engine 380, procedure planning engine382, navigation engine 384, and context analysis module 386. Understoodis that the system 200 (FIGS. 1 and 2) is not intended to be limited tothe components shown in the several figures of the Drawing. One or morecomponents of the control and processing 300 may be provided as anexternal component or device. In one alternative embodiment, navigationmodule 484 may be provided as an external navigation system that isintegrated with control and processing unit 300.

Embodiments of the system 200 of FIG. 2 may be implemented usingprocessor 302 without additional instructions stored in memory 304.Embodiments may also be implemented using the instructions stored in thememory 304 for execution by one or more general purpose microprocessors.

Thus, the disclosure is not limited to a specific configuration ofhardware, firmware, and/or software. While some embodiments can beimplemented in fully functioning computers and computer systems, variousembodiments are capable of being distributed as a computing product in avariety of forms and are capable of being applied regardless of theparticular type of machine or computer readable media used to actuallyeffect the distribution. At least some aspects disclosed can beembodied, at least in part, in software. That is, the techniques may becarried out in a computer system or other data processing system inresponse to its processor, such as a microprocessor, executing sequencesof instructions contained in a memory, such as ROM, volatile RAM,non-volatile memory, cache or a remote storage device. A computerreadable storage medium can be used to store software and data whichwhen executed by a data processing system causes the system to performvarious methods. The executable software and data may be stored invarious places including for example ROM, volatile RAM, nonvolatilememory and/or cache. Portions of this software and/or data may be storedin any one of these storage devices.

The preceding exemplary embodiments involve systems and methods in whicha device is intra-operatively configured based on the identification ofa medical instrument. In other example embodiments, one or more devicesmay be automatically controlled and/or configured by determining one ormore context measures associated with a medical procedure. A “contextmeasure”, as used herein, refers to an identifier, data element,parameter or other form of information that pertains to the currentstate of a medical procedure. In one example, a context measure maydescribe, identify, or be associated with, the current phase or step ofthe medical procedure. In another example, a context measure mayidentity the medical procedure, or the type of medical procedure, thatis being performed. In another example, a context measure may identifythe presence of a tissue type during a medical procedure. In anotherexample, a context measure may identify the presence of one or morefluids, such as biological fluids or non-biological fluids (e.g. washfluids) during the medical procedure, and may further identify the typeof fluid. Each of these examples relate to the image-basedidentification of information pertaining to the context of the medicalprocedure.

Examples of computer-readable storage media include, but are not limitedto, recordable and non-recordable type media such as volatile andnon-volatile memory devices, ROM, RAM, flash memory devices, floppy andother removable disks, magnetic disk storage media, optical storagemedia (e.g., compact discs (CDs), digital versatile disks (DVDs), etc.),among others. The instructions can be embodied in digital and analogcommunication links for electrical, optical, acoustical or other formsof propagated signals, such as carrier waves, infrared signals, digitalsignals, and the like. The storage medium may be the internet cloud, ora computer readable storage medium such as a disc.

At least some of the methods described herein are capable of beingdistributed in a computer program product comprising a computer readablemedium that bears computer usable instructions for execution by one ormore processors, to perform aspects of the methods described. The mediummay be provided in various forms such as, but not limited to, one ormore diskettes, compact disks, tapes, chips, USB keys, external harddrives, wire-line transmissions, satellite transmissions, internettransmissions or downloads, magnetic and electronic storage media,digital and analog signals, and the like. The computer useableinstructions may also be in various forms, including compiled andnon-compiled code.

While the present disclosure describes various embodiments forillustrative purposes, such description is not intended to be limited tosuch embodiments. On the contrary, the applicant's teachings describedand illustrated herein encompass various alternatives, modifications,and equivalents, without departing from the embodiments, the generalscope of which is defined in the appended claims. Except to the extentnecessary or inherent in the processes themselves, no particular orderto steps or stages of methods or processes described in this disclosureis intended or implied. In many cases the order of process steps may bevaried without changing the purpose, effect, or import of the methodsdescribed.

Information as herein shown and described in detail is fully capable ofattaining the above-described object of the present disclosure, thepresently preferred embodiment of the present disclosure, and is, thus,representative of the subject matter which is broadly contemplated bythe present disclosure. The scope of the present disclosure fullyencompasses other embodiments which may become apparent to those skilledin the art, and is to be limited, accordingly, by nothing other than theappended claims, wherein any reference to an element being made in thesingular is not intended to mean “one and only one” unless explicitly sostated, but rather “one or more.” All structural and functionalequivalents to the elements of the above-described preferred embodimentand additional embodiments as regarded by those of ordinary skill in theart are hereby expressly incorporated by reference and are intended tobe encompassed by the present claims. Moreover, no requirement existsfor a system or method to address each and every problem sought to beresolved by the present disclosure, for such to be encompassed by thepresent claims. Furthermore, no element, component, or method step inthe present disclosure is intended to be dedicated to the publicregardless of whether the element, component, or method step isexplicitly recited in the claims. However, that various changes andmodifications in form, material, work-piece, and fabrication materialdetail may be made, without departing from the spirit and scope of thepresent disclosure, as set forth in the appended claims, as may beapparent to those of ordinary skill in the art, are also encompassed bythe disclosure.

What is claimed is:
 1. A method for manufacturing a medical probecomprising: assembling a multichannel fiber bundle comprising at leasttwo optical fibers associated with distinct optical probe channels;micro-fabricating a common monolithic optical probe tip structure via a3D laser printing process to concurrently engage and respectivelyoptically couple said optical probe tip structure with a common distalend of each of said at least two optical fibers in ultimately definingrespective predesigned optical channel paths within said probe tipstructure; wherein said micro-fabricating comprises micro-fabricatingrespective probe tip ports or waveguides to controllably engage andrespectively optically couple said optical probe tip structure with eachof said at least two optical fibers.
 2. The method of claim 1, whereinsaid micro-fabricating comprises micro-fabricating said structuredirectly upon said common distal end of said at least two opticalfibers.
 3. The method of claim 1, wherein said micro-fabricatingcomprises micro-fabricating a common probe tip port to controllablyengage said fiber bundle and respectively optically couple said opticalprobe tip structure with each of said at least two optical fibers. 4.The method of claim 1, wherein said micro-fabricating comprisesmicro-fabricating a respective lens element for each of said respectivepredesigned optical channel paths.
 5. The method of claim 1, whereinsaid micro-fabricating comprises fabricating a beam steering surfacewithin said optical probe tip structure to redirect at least one of saidpredesigned optical channel paths at an angle relative to said fiberbundle.
 6. The method of claim 1, wherein said at least two opticalfibers comprise at least one illumination fiber for operative couplingto an illumination light source in relaying illumination via said probetip structure, and at least one collection fiber for operative couplingto a detector in collecting light in response to said illumination,wherein the method further comprises: defining one or morewavelength-selective features within said optical probe tip structure togovern a spectral response thereof along a corresponding one of saidpredesigned optical channel paths.
 7. The method of claim 6, whereinsaid defining comprises depositing a wavelength-selective coating upon adesignated internal probe tip structure surface fabricated to intersectsaid corresponding one of said predesigned optical channel paths.
 8. Themethod of claim 6, wherein said defining comprises integrallyfabricating a texturized wavelength-selective surface within said probetip structure to intersect at least one of said predesigned opticalchannel paths.